Pulse Generator System for Promoting Desynchronized Firing of Recruited Neural Populations

ABSTRACT

An Implantable Pulse Generator (IPG) is disclosed that is capable of sensing a degree to which recruited neurons in a patient&#39;s tissue are firing synchronously, and of modifying a stimulation program to promote desynchronicity and to reduce paresthesia. An evoked compound action potential (ECAP) of the recruited neurons is sensed as a measure of synchronicity by at least one non-active electrode. An ECAP algorithm operable in the IPG assesses the shape of the ECAP and determines one or more ECAP shape parameters that indicate whether the recruited neurons are firing synchronously or desynchronously. If the shape parameters indicate significant synchronicity, the ECAP algorithm can adjust the stimulation program to promote desynchronous firing.

CROSS REFERENCE TO RELATED APPLICATIONS

This is a continuation application of U.S. patent application Ser. No.17/199,185, filed Mar. 11, 2021 (allowed), which is a continuationapplication of U.S. patent application Ser. No. 16/417,076, filed May20, 2019 (now U.S. Pat. No. 10,960,211), which is a continuationapplication of U.S. patent application Ser. No. 15/428,612, filed Feb.9, 2017 (now U.S. Pat. No. 10,406,368), which is a non-provisional ofU.S. Provisional Patent Application Ser. No. 62/324,801, filed Apr. 19,2016. These applications are incorporated by reference in theirentirety, and priority is claimed to each

FIELD OF THE INVENTION

The present invention relates generally to medical device systems, andmore particularly to a pulse generator system operable to promotedesynchronized firing of recruited neural populations.

BACKGROUND

Implantable stimulation devices deliver electrical stimuli to nerves andtissues for the therapy of various biological disorders, such aspacemakers to treat cardiac arrhythmia, defibrillators to treat cardiacfibrillation, cochlear stimulators to treat deafness, retinalstimulators to treat blindness, muscle stimulators to producecoordinated limb movement, spinal cord stimulators to treat chronicpain, cortical and Deep Brain Stimulators (DBS) to treat motor andpsychological disorders, and other neural stimulators to treat urinaryincontinence, sleep apnea, shoulder subluxation, etc. The descriptionthat follows will generally focus on the use of the invention within aSpinal Cord Stimulation (SCS) system, such as that disclosed in U.S.Pat. No. 6,516,227. However, the present invention may findapplicability with any Implantable Medical Device (IPG) or in any IPGsystem, such as in a Deep Brain Stimulation (DBS) system as disclosed inU.S. Pat. No. 9,119,964.

An SCS system typically includes an Implantable Pulse Generator (IPG) 10shown in plan and cross-sectional views in FIGS. 1A and 1B. The IPG 10includes a biocompatible device case 30 is configured for implantationin a patient's tissue that holds the circuitry and battery 36 (FIG. 1B)necessary for the IPG to function. The IPG 10 is coupled to electrodes16 via one or more electrode leads 14 that form an electrode array 12.The electrodes 16 are configured to contact a patient's tissue and arecarried on a flexible body 18, which also houses the individual leadwires 20 coupled to each electrode 16. The lead wires 20 are alsocoupled to proximal contacts 22, which are insertable into leadconnectors 24 fixed in a header 28 on the IPG 10, which header cancomprise an epoxy for example. Once inserted, the proximal contacts 22connect to header contacts 26 in the lead connectors 24, which are inturn coupled by electrode feedthrough pins 34 through an electrodefeedthrough 32 to circuitry within the case 30 (connection not shown).

In the illustrated IPG 10, there are thirty-two lead electrodes (E1-E32)split between four leads 14, with the header 28 containing a 2×2 arrayof lead connectors 24 to receive the leads' proximal ends. However, thenumber of leads and electrodes in an IPG is application specific andtherefore can vary. In a SCS application, the electrode leads 14 aretypically implanted proximate to the dura in a patient's spinal cord,and when a four-lead IPG 10 is used, these leads can be split with twoon each of the right and left sides. The proximal contacts 22 aretunneled through the patient's tissue to a distant location such as thebuttocks where the IPG case 30 is implanted, at which point they arecoupled to the lead connectors 24. As also shown in FIG. 1A, one or moreflat paddle leads 15 can also be used with IPG 10, and in the exampleshown thirty two electrodes 16 are positioned on one of the generallyflat surfaces of the head 17 of the paddle lead, which surface wouldface the dura when implanted. In other IPG examples designed forimplantation directly at a site requiring stimulation, the IPG can belead-less, having electrodes 16 instead carried by the case of the IPGfor contacting the patient's tissue.

As shown in the cross section of FIG. 1B, the IPG 10 includes a printedcircuit board (PCB) 40. Electrically coupled to the PCB 40 are thebattery 36, which in this example is rechargeable; other circuitry 46coupled to top and/or bottom surfaces of the PCB 40, including amicrocontroller or other control circuitry necessary for IPG operation;a telemetry antenna—42 a and/or 42 b—for wirelessly communicating datawith an external controller 50 (FIG. 2 ); a charging coil 44 forwirelessly receiving a magnetic charging field from an external charger(not shown) for recharging the battery 36; and the electrode feedthroughpins 34 (connection to circuitry not shown). If battery 36 is permanentand not rechargeable, charging coil 44 would be unnecessary.

Either or both of telemetry antennas 42 a and 42 b can be used totranscutaneously communicate data through the patient's tissue to anexternal device such as the external controller 50 shown in FIG. 2 .Antennas 42 a and 42 b are different in shape and in the electromagneticfields they employ. Telemetry antenna 42 a comprises a coil, which canbi-directionally communicate with an external device via a magneticinduction communication link, which comprises a magnetic field oftypically less than 10 MHz operable in its near-field to communicate ata distance of 12 inches or less for example. Telemetry antenna 42 bcomprises a short-range Radio-Frequency (RF) antenna that operates inaccordance with a short-range RF communication standard and itsunderlying modulation scheme and protocol to bi-directionallycommunicate with an external device along a short-range RF communicationlink. Short-range RF communication link typically operates usingfar-field electromagnetic waves ranging from 10 MHz to 10 GHz or so, andallows communications between devices at distances of about 50 feet orless. Short-range RF standards operable with antenna 42 b include, forexample, Bluetooth, BLE, NFC, Zigbee, WiFi (802.11x), and the MedicalImplant Communication Service (MICS) or the Medical DeviceRadiocommunications Service (MDRS). Short-range RF antenna 42 b can takeany number of well-known forms for an electromagnetic antenna, such aspatches, slots, wires, etc., and can operate as a dipole or a monopole.IPG 10 could contain both the coil antenna 42 a and the short-range RFantenna 42 b to broaden the types of external devices with which the IPG10 can communicate, although IPG 10 may also include only one of antenna42 a and 42 b.

Implantation of IPG 10 in a patient is normally a multi-step process, asexplained with reference to FIG. 3 . A first step involves implantationof the distal ends of the lead(s) 14 or 15 with the electrodes 16 intothe spinal column 60 of the patient through a temporary incision 62 inthe patient's tissue 5. (Only two leads 14 with sixteen total electrodes16 are shown in FIG. 3 for simplicity). The proximal ends of the leads14 or 15 including the proximal contacts 22 extend externally from theincision 62 (i.e., outside the patient), and are ultimately connected toan External Trial Stimulator (ETS) 70. The ETS 70 is used during a trialstimulation phase to provide stimulation to the patient, which may lastfor two or so weeks for example. To facilitate the connection betweenthe leads 14 or 15 and the ETS 70, ETS extender cables 80 may be usedthat include receptacles 82 (similar to the lead connectors 24 in theIPG 10) for receiving the proximal contacts 22 of leads 14 or 15, andconnectors 84 for meeting with ports 72 on the ETS 70, thus allowing theETS 70 to communicate with each electrode 16 individually. Onceconnected to the leads 14 or 15, the ETS 70 can then be affixed to thepatient in a convenient fashion for the duration of the trialstimulation phase, such as by placing the ETS 70 into a belt worn by thepatient (not shown). ETS 70 includes a housing 73 for its controlcircuitry, antenna, etc., which housing 73 is not configured forimplantation in a patient's tissue.

The ETS 70 essentially mimics operation of the IPG 10 to providestimulation to the implanted electrodes 16, and thus includes contains abattery within its housing along with stimulation and communicationcircuitry similar to that provided in the IPG 10. Thus, the ETS 70allows the effectiveness of stimulation therapy to be verified for thepatient, such as whether therapy has alleviated the patient's symptoms(e.g., pain). Trial stimulation using the ETS 70 further allows for thedetermination of particular stimulation program(s) that seems promisingfor the patient to use once the IPG 10 is later implanted into thepatient. A stimulation program may specify for example which of theelectrodes 16 are to be active and used to issue stimulation pulses;whether those active electrodes are to act as anodes or cathodes; thecurrent or voltage amplitude (A) of the stimulation pulses; the pulsewidth (PW) of the stimulation pulses; and frequency (f) of thestimulation pulses, as well as other parameters.

The clinician programmer system of FIG. 3 can also be used generally bya clinician to communicate with and program the IPG 10 once it is fullyimplanted in a patient. Such communication again would occur viacommunication link 92. Thus the clinician programmer system may be usedduring patient check-ups for example to update the stimulation programthe IPG 10 is running.

An example of stimulation pulses as prescribed by a particularstimulation program is illustrated in FIG. 4 . As shown, and as istypical in an IPG, each stimulation pulse is biphasic, meaning itcomprises a first pulse phase followed essentially immediatelythereafter by an opposite polarity pulse phase. The pulse width (PW)could comprise the duration of either of the pulse phases individuallyas shown, or could comprise the entire duration of the biphasic pulseincluding both pulse phases.

Biphasic pulses are useful because the second pulse phase can activelyrecover any charge build up after the first pulse phase residing oncapacitances (such as the DC-blocking capacitors 107 discussed laterwith respect to FIG. 7 ) in the current paths between the activeelectrodes. In the example stimulation program shown, electrode E4 isselected as the anode electrode while electrode E5 is selected as thecathode electrode. The pulses as shown comprise pulses of constantcurrent, and notice that the amplitude of the current at any point intime is equal but opposite such that current injected into the patient'stissue by one electrode (e.g., E4) is removed from the tissue by theother electrode (E5). Notice also that the area of the first and secondpulses phases are equal, ensuring active charge recovery of the sameamount of charge during each pulse phase. Although not shown, more thantwo electrodes can be active at any given time. For example, electrodeE4 could comprise an anode providing a +10 mA current pulse amplitude,while electrodes E3 and E5 could both comprise cathodes with −7 mA and−3 mA current pulse amplitudes respectively.

Referring again to FIG. 3 , the stimulation program executed by the ETS70 can be provided or adjusted via a wired or wireless link 92 (wirelessshown) from a clinician programmer 90. As shown, the clinicianprogrammer 90 comprises a computer-type device, and may communicatewirelessly with the ETS 70 via link 92, which link may comprise magneticinductive or short-range RF telemetry schemes as already described.Should the clinician programmer 90 lack a communication antenna, acommunication head or wand 94 may be wired to the computer which has acommunication antenna. Thus, the ETS 70 and the clinician's programmer90 and/or its communication head 94 may include antennas compliant withthe telemetry scheme chosen. Clinician programmer 90 may be as describedin U.S. Patent Application Publication 2015/0360038. External controller50 (FIG. 2 ) may also communicate with the ETS 70 to allow the patientmeans for providing or adjusting the ETS 70's stimulation program.

At the end of the trial stimulation phase, a decision is made whether toabandon stimulation therapy, or whether to provide the patient with apermanent IPG 10 such as that shown in FIGS. 1A and 1B. Should it bedetermined that stimulation therapy is not working for the patient, theleads 14 or 15 can be explanted from the patient's spinal column 60 andincision 62 closed in a further surgical procedure.

By contrast, if stimulation therapy is effective, IPG 10 can bepermanently implanted in the patient as discussed above. (“Permanent” inthis context generally refers to the useful life of the IPG 10, whichmay be from a few years to a few decades, at which time the IPG 10 wouldneed to be explanted and a new IPG 10 implanted). Thus, the IPG 10 wouldbe implanted in the correct location (e.g., the buttocks) and connectedto the leads 14 or 15, and then temporary incision 62 can be closed andthe ETS 70 dispensed with. The result is fully-implanted stimulationtherapy solution. If a particular stimulation program(s) had beendetermined during the trial stimulation phase, it/they can then beprogrammed into the IPG 10, and thereafter modified wirelessly, usingeither the external programmer 50 or the clinician programmer 90.

BRIEF DESCRIPTION OF THE DRAWINGS

FIGS. 1A and 1B respectively show an Implantable Pulse Generator (IPG)in plan and cross sectional views, in accordance with the prior art.

FIG. 2 shows a hand-held external controller for communicating with anIPG, in accordance with the prior art.

FIG. 3 shows a clinician programming system for communicating with anIPG or an External Trial Stimulator (ETS), in accordance with the priorart.

FIG. 4 shows an original stimulation program deemed effective for apatient, in accordance with the prior art.

FIG. 5 shows a graph of an action potential of a neuron, in accordancewith the prior art.

FIG. 6 shows an electric field produced in a patient's tissue forrecruiting neurons to fire, in accordance with the prior art.

FIG. 7 shows an improved IPG including control circuitry programmed withan Evoked Compound Action Potential (ECAP) algorithm, and furtherincluding sensing circuitry for sensing an ECAP at a sense electrode, inaccordance with an example of the invention.

FIGS. 8A and 8B show an original stimulation program, the resultinggeneration of an ECAP (with examples of resulting synchronous anddesynchronous ECAPs), and detection of that ECAP by ECAP algorithm inthe improved IPG, in accordance with an example of the invention.

FIG. 9 shows a flow chart of the ECAP algorithm, in accordance with anexample of the invention.

FIGS. 10A and 10B show a first manner in which the ECAP algorithm canadjust the original stimulation program to promote desynchronous firingof recruited neurons through the addition of active electrode, inaccordance with an example of the invention.

FIGS. 11A and 11B show a second manner in which the additional activeelectrode produces a pulse that is not overlapping with the pulses inthe original stimulation program, in accordance with an example of theinvention.

FIGS. 12A and 12B show a third manner in which the additional activeelectrode produces pulse that are overlapping with the pulses in theoriginal stimulation program, in accordance with an example of theinvention.

FIGS. 13A and 13B show a fourth manner in which the additional activeelectrode produces pulses with a frequency different from the pulses inthe original stimulation program, in accordance with an example of theinvention.

FIGS. 14A and 14B show a fifth manner not using an additional activeelectrode, in which the amplitude of the pulses in the originalstimulation program is modified, in accordance with an example of theinvention.

FIGS. 15A and 15B show a sixth manner not using an additional activeelectrode, in which the pulse widths of the pulses in the originalstimulation program are modified, in accordance with an example of theinvention.

DETAILED DESCRIPTION

Particularly as concerns SCS therapy, there is evidence to suggest thatproviding stimulation pulses at relatively high frequencies (e.g., >1kHz) can have therapeutic benefits when compared to lower-frequencystimulation pulses. In particular, it has been reported thathigher-frequency stimulation may reduce certain side effects that canaccompany lower-frequency stimulation. Specifically, higher-frequencystimulation may reduce paresthesia—a tingling or prickling sensation.

The inventor theorizes that the benefits of high frequency stimulationrelate to inherent limitations regarding the frequency at which neuronscan respond to stimulation. When a neuron is recruited by electricalstimulation, it will issue an action potential—that is, the neuron will“fire.” An action potential for a typical neuron is shown in FIG. 5 .Should electrical recruitment cause the neuron's resting state (e.g.,−70 mV as measured from inside the cell) to exceed a threshold (e.g.,−55 mV), the neuron will depolarize (“A”), repolarize (“B”), and refract(“C”) before coming to rest again. If electrical stimulation continues,the neuron will fire again at some later time. Note that the actionpotential does not change in magnitude for a given neuron; in otherwords, the action potential does not change with the strength ofstimulation. Instead, a strong stimulus will increase the frequency atwhich action potentials are issued.

However, there is a limit to how quickly a given neuron can fire. Eachneuron is unique in its shape and size, and thus can fire at its owninherent maximum frequency. Consider FIG. 6 , which illustrates theexample of FIG. 4 in which electrodes E4 and E5 on lead 14 are used toproduce pulses. Such stimulation produces an electric field in a volume95 of the patient's tissue 5 around the selected electrodes. Some of theneurons within the electric field volume 95 will be recruited and fire,particularly those proximate to the cathodic electrode E5. Hopefully thesum of the neurons firing within volume 95 will mask signals indicativeof pain, thus providing the desired therapy.

The inventor reasons that if high frequency stimulation is used that isgenerally higher than the maximum frequency at which the neurons canfire (and if the stimulation is suitably strong), the recruited neuronswithin volume 95 will be unable to fire at the frequency of thestimulation. Instead, each neuron will be limited to firing at itsmaximum frequency, which again will be different for each neuron. Thus,the firing of the neurons within volume 95 will be desynchronized withdifferent neurons firing at different times. By contrast, the inventorhypothesizes that if low frequency stimulation is used that is generallylower than the maximum neuronal frequency, the recruited neurons withinvolume 95 will all fire at the frequency of the stimulation and at thesame time. In other words, the neurons will fire synchronously.

The inventor reasons further that synchronous firing of the neurons atlow frequencies is responsible for the undesired side effect ofparesthesia, and that desynchronized firing at higher frequenciesmitigates this effect. However, the inventor finds this circumstanceunfortunate, because it is not a simple matter to provide stimulationpulses at high frequencies. For one, high frequency stimulation requiresthat the circuitry that produces the pulses in the IPG 10 also switch athigh frequencies. High frequency switching of the IPG's circuitry ismore power consumptive, and thus requires a higher draw from the IPGbattery 36. As a result, the battery 36 must either be made biggerincreasing IPG size, or the battery must be wirelessly recharged morefrequently, both of which are undesired.

The inventor thus provides an IPG or ETS that is capable of sensing thedegree to which recruited neurons are firing synchronously. Sensedsynchronicity is preferably also used in a closed loop fashion by theIPG to modify an original stimulation program the IPG is executing,which original stimulation program is otherwise generally providing goodtherapeutic result for the patient, although perhaps with the sideeffect of paresthesia. In one example, a neural response to the originalstimulation program, particularly an evoked compound action potential(ECAP) of the recruited neurons, is sensed as a measure ofsynchronicity. At least one non-active electrode senses the resultingECAP, which is digitized and sent to the IPG's control circuitry. AnECAP algorithm assesses the shape of the ECAP and determines one or moreECAP shape parameters that indicate whether the recruited neurons arefiring synchronously or desynchronously. If the shape parametersindicate a high degree of synchronicity, the ECAP algorithm can adjustthe stimulation program in one or more manners to promote desynchronousfiring, thus reducing paresthesia. The ECAP algorithm can operate toadjust an original stimulation program even if it is otherwise operableat generally low frequencies (<1 kHz), although it can be used to assessand promote desynchronicity at higher frequencies as well.

An improved IPG 100 operable as just described is shown in FIG. 7 .Although described in the context of an IPG 100, it should be realizedthat the invention could also be embodied in an external stimulator,such as an External Trial Stimulation (e.g., ETS 70, FIG. 3 ) thatgenerally mimics the operation of an IPG as explained earlier.

The IPG 100 includes control circuitry 102 into which an ECAP algorithm124 can be programmed, which may comprise a microcontroller for examplesuch as Part Number MSP430, manufactured by Texas Instruments, which isdescribed in data sheets posted on the Internet. Other types of controlcircuitry may be used in lieu of a microcontroller as well, such asmicroprocessors, FPGAs, DSPs, or combinations of these, etc. Controlcircuitry may also be formed in whole or in part in one or moreApplication Specific Integrated Circuits (ASICs), as described in U.S.Patent Application Publication 2012/0095529 and USPs 9,061,140 and8,768,453, which are incorporated herein by reference.

A bus 118 provides digital control signals to stimulation circuitry 105,including one or more Digital-to-Analog converters (DACs) 104, which areused to produce currents or voltages of prescribed amplitudes (A) forthe stimulation pulses, and with the correct timing (PW, f). As shown,the DACs include both PDACs which source current to one or more selectedanode electrodes, and NDACs which sink current from one or more selectedcathode electrodes. A switch matrix 106 is used to route one or morePDACs and one or more NDACs to any of the electrodes 16 via bus 116, andthus effectively selects the anode and cathode electrodes. In short,buses 118 and 116 generally set the stimulation program the IPG 100 isrunning. The illustrated stimulation circuitry 105 for producingstimulation pulses and delivering them to the electrodes is merely oneexample. Other approaches may be found for example in USPs 8,606,362 and8,620,436.

Notice that the current paths to the electrodes 16 include theDC-blocking capacitors 107 alluded to earlier, which as known provideadditional safety by preventing the inadvertent supply of DC current toan electrode and to a patient's tissue. As discussed earlier,capacitances such as these can become charged as stimulation currentsare provided, providing the impetus for the use of biphasic pulses.

Any of the electrodes 16 can preferably be used to sense the ECAPdescribed earlier, and thus each electrode is further coupleable to atleast one sense amp 110. In the example shown, all of the electrodesshare a single sense amp 110, and thus any one sensing electrode can becoupled to the sense amp 110 at a given time per multiplexer 108, ascontrolled by bus 114. This is however not strictly necessary, andinstead each electrode can be coupleable to its own dedicated sense amp110. The analog waveform comprising the ECAP, described further below,is preferably converted to digital signals by an Analog-to-Digitalconverter 112, which may also reside within the control circuitry 102.

Notice that connection of the electrodes 16 to the sense amp(s) 110preferably occurs through the DC-blocking capacitors 107, such thatcapacitors are between the electrodes and the sense amp(s). This ispreferred so as to not undermine the safety provided by the DC-blockingcapacitors 107.

Once the digitized ECAP is received at the control circuitry 102, it isprocessed by the ECAP algorithm 124 to determine one or more ECAP shapeparameters. The waveform to the right in FIG. 7 shows the basic shape ofan ECAP. Unlike the action potential shown for an individual neuron inFIG. 5 , the ECAP measured external to the cell will be inverted, butwill otherwise generally resemble the shape of a signal actionpotential. As it name implies, ECAP comprises a compound (summation) ofvarious action potentials as issued from a plurality of neurons, and itsize will thus depend on how many neurons are firing. Generallyspeaking, an ECAP can vary between 100 microVolts to tens of milliVolts.Note that the DC blocking capacitor 107 through which the ECAPs passwill remove any DC components in the signal, which is thus referenced to0 Volts. If necessary, the sensed ECAP signal can be level shifted tooccur within a range that the electronics in the IPG 100 can handle,such as between 3 Volts and ground.

FIGS. 8A and 8B illustrate a particular stimulation program, theresulting generation of an ECAP, and detection of that ECAP. Thestimulation program is defined as before by various stimulationparameters, such as pulses of a particular amplitude, pulse width, andfrequency, although these parameters are not labeled in FIG. 8B. In theexample stimulation program shown, electrode E4 is selected to operateas an anode (+), and electrode E5 as a cathode (−), as occurred in FIG.4 . It is assumed that this particular stimulation program has beenchosen as one that generally provides good therapeutic results for aparticular patient, although perhaps with the side effect ofparesthesia. This can be said to comprise an “original” stimulationprogram, may have been determined during ETS testing (FIG. 3 ) orotherwise.

Once stimulation begins (at time=0), an ECAP will be produced comprisingthe sum of the action potentials of neurons recruited and hence firingin electric field volume 95. As shown in FIG. 8A, the ECAP will movethrough the patient's tissue via neural conduction with a speed of about5 cm/1 ms. In the example shown, the ECAP moves to the right, which isin the direction toward the brain. However, the ECAP will also move inthe other direction as well toward the periphery of the patient.

A single sense electrode (S) has been chosen to sense the ECAP as itmoves past, which in this example is electrode E9. Selection of anappropriate sense electrode can be determined by the ECAP algorithm 124operable in the control circuitry 102 based on a number of factors. Forexample, it is preferable that a sense electrode S be sensibly chosenwith respect to the active electrodes, such that the electric field 95produced around the active electrodes will have ceased by the time thesense electrode is enabled to sense the ECAP. This simplifies ECAPdetection at the sense electrode, because voltages present in theelectric field 95 will not interfere with and potentially mask the ECAP.In this regard, it is useful for the ECAP algorithm 124 to know thepulse width of the stimulation program, the extent of the size of theelectric field 95 (which can be estimated), the speed at which the ECAPis expected to travel, and the distance between electrodes 16 in theelectrode array 12, e.g., along a particular straight lead 14 or apaddle lead 15 (FIG. 1A).

In FIG. 8A for example, assume that the pulse width (of both phases ofthe biphasic pulse) is 0.5 ms as shown, and that electrode E9 isgenerally 2.5 cm away (d) from the active electrodes (and hence theirelectric field 95). When the ECAP is formed in the electric field 95 atthe outset of stimulation at time=0, it will arrive at electrode E9after some delay 130 in accordance with the speed at which the ECAPmoves (e.g., 5 cm/1 ms). In other words, the ECAP will start to passsense electrode E9 at 0.5 ms. Because the stimulation pulse and electricfield 95 would have ceased at this point, sense electrode E9 should notsense any voltage relating to the electric field, and should only sensethe ECAP. Thus, the ECAP algorithm 124 can enable sensing of the ECAPstarting at time=0.5 ms after the start of the stimulation pulse. Suchenabling can be controlled by controlling multiplexer 108 via bus 114(FIG. 7 ) to pass the input from sense electrode E9 to the sense amp110, the ADC 112, and ultimately the ECAP algorithm 124. Sensing canlast for as long as necessary to detect at least some aspects of theshape of the resulting ECAP. For example, sensing can last for a longenough time to allow the polarization and refraction peaks in the ECAPto be detected, which may comprise 3 ms for example.

It should be noted that it is not strictly necessary that sensing occurat an electrode that would not experience interference from the electricfield 95, as masking techniques can be used to subtract voltages presentin the electric field. Such masking techniques are described for examplein M. Hughes, “Fundamentals of Clinical ECAP Measures in CochlearImplants: Part 1: Use of the ECAP in Speech Processor Programming (2ndEd.),” Audiology Online (Nov. 8, 2010); and I. Akhoun et al.,“Electrically evoked compound action potential artifact rejection byindependent component analysis: Technique validation,” Hearing Research302 pp. 60-73 (2013), which are both incorporated herein by reference.Such masking techniques may allow electrodes closer to the activeelectrodes (e.g., E6) to be chosen as sense electrodes.

Further, the ECAP algorithm 124 could also choose more than oneelectrode to act as a sense electrode. For example, ECAP algorithm 124may sense the traveling ECAP at electrodes E6, E7, E8, E9, etc. Thiswould require timing control, because E6 would be sensed before E7,etc., and might further require circuitry changes to accommodate sensingthe ECAP at different electrodes at overlapping points in time. Forexample, each electrode might in this example require its own timingcontrol (mux 108), and its own sense amp 110 and ADC 112, although thisisn't illustrated in FIG. 7 .

A practical aspect that could affect sensing ECAPs in IPG 100 relates topassive charge recovery. As discussed earlier, the use of biphasicpulses are preferred in an IPG to actively recover charge during thesecond pulse phase that may have built up across capacitive elements(such as the DC blocking capacitor 107) during the first pulse phase.Because active charge recovery may not be perfect, IPG 100 mayadditionally include passive charge recovery as implemented by switches122 shown in FIG. 7 . Passive charge recovery switches 122 arecontrolled by bus 120 issued from the control circuitry 102, and act toconnect the inside plate of the DC blocking capacitors 107 to a commonpotential (Vref). When this occurs, the DC blocking capacitors 107 areconnected in parallel between the common potential and the patient'stissue, which helps to equilibrate the charge across the capacitors anhence recover any remaining charge. Passive charge recovery usingswitches 122 typically occurs after the last phase of each stimulationpulse, as shown by the small, exponentially-decreasing waveform in FIG.8B. Passive charge recovery might otherwise overlap in time with periodsin which ECAP sensing is enabled. This could cause a problem for ECAPsensing, because it would place the common potential on the inputs tothe multiplexer that carry the ECAP signals. As a result, controlcircuitry 102 will preferably not close the passive recovery switch 122associated with the sense electrode being sensed, although all otherswitches 122 may be closed. Alternatively, control circuitry may closeonly the switches coupled to the active electrodes (E4, E5). Once ECAPhas been sensed, control circuitry 102 may return to closing the senseelectrode's switch 122 if desired.

FIG. 8B illustrates ECAP as sensed assuming two conditions: first, whenthe recruited neurons within electric field 95 fire in a generallysynchronized fashion; and second, when the recruited neurons fire in agenerally desynchronized fashion, which as noted before is theorized tobe desirable in reducing side effects such as paresthesia. Notice thatthe shapes of the ECAPs for these two conditions are different. In thesynchronized case, the recruited neurons generally fire at the sametime, and so their cumulative effect results in a waveform with a higherand sharper peak, that is, in which its height H1 is relatively large,and its full-width half-maximum FWHM1 is relatively small. By contrast,in the desynchronized case, the recruited neurons fire at differenttimes, and so their cumulative effect results in a waveform with asmaller and broader peak in which H2 is relatively small and FWHM2 isrelatively large. Other parameters may also be useful in analyzing theECAP, such as various slopes, the timing of the peaks, etc., but shapeparameters H and FWHM are illustrated for simplicity.

Although only one ECAP is shown for each condition shown in FIG. 8B, itshould be understood that an ECAP will be produced at the beginning ofeach stimulation pulse. Thus, the ECAP algorithm 124 may take more thanone ECAP measurement—for example, after several consecutive pulses—andaverage the shape parameters (e.g., H, FWHM) for each. Shape parametersfor measured ECAPs taken at different sensing electrodes (e.g., at E6,E7, etc.) can be averaged as well.

Once ECAP has been measured and it shape parameters determined, ECAPalgorithm 124 can assess these shape parameters to discern the degree towhich stimulation appears to be synchronous or desynchronous, and canautomatically adjust the original stimulation program in one or moremanners to try and promote desynchronicity. Determining the degree ofsynchronicity can occur in one simple example by comparing the shapeparameters to thresholds, for example, by comparing the height H of theECAP to a first threshold T1, and/or by comparing the width (e.g., FWHM)of the ECAP to a second threshold T2. Again, other shape parameters canbe used, and more than one shape parameter may be considered indetermining synchronicity. If it is determined that the ECAP that is toosynchronous, for example, if H>T1, and/or if FWHM<T2, then the originalstimulation program can be adjusted in one or more manners to try andpromote desynchronicity.

FIG. 9 shows an example of the operation of the ECAP algorithm 124, andmany of its steps have already been discussed above, but are reviewedhere for completeness. Prior to operation of the ECAP algorithm, anoriginal stimulation program has preferably been chosen that iseffective for the patient (step 140). This isn't however strictlynecessary, and instead the ECAP algorithm 124 may be used in determiningan original stimulation program, for example, one that initially seemsto provide good desynchronicity during the ETS stage, but which could bemodified further later.

Once an original stimulation program is chosen, the ECAP algorithm 124can choose one or more electrodes to act as a sense electrode (S) (step142), as described above. Stimulation can then be provided using theoriginal stimulation program (step 144), and one or more ECAP measured(step 146) at the sense electrode(s). As noted above, a plurality ofECAPs can be measured. For the ECAP(s), at least one ECAP shapeparameter (e.g., H, FWHM) can be determined (step 148), and if necessaryaveraged from the plurality of ECAP(s). The ECAP algorithm 124 can thenassess the shape parameter(s) to determine a degree of synchronicity ofthe firing of the recruited neurons (step 150), which may involvecomparison of the parameters to one or more thresholds as describedearlier.

If the stimulation appears to provide significantly desynchronizedfiring, the ECAP algorithm 124 can return to step 144 and continue toprovide the stimulation program without adjustment, although the processcan continue to monitor ECAP and make adjustment in the future ifneeded. If the stimulation appears to provide significantly synchronizedfiring, the stimulation program can be adjusted, and manners of doing soare discussed subsequently with respect to FIGS. 10A-15B. Generallyspeaking, adjustment may involve adjusting any stimulation parameter,including which of the electrodes 16 are to be active; whether thoseactive electrodes are to act as anodes or cathodes; the current orvoltage amplitude (A) of the stimulation pulses; the pulse width (PW) ofthe stimulation pulses; and frequency (f) of the stimulation pulses.After adjustment, ECAP(s) can again be measured (step 146), shapeparameter(s) determines (step 148), and assessed (step 150) to see ifsignificant desynchronization has been achieved. If not, the stimulationprogram can be adjusted again, and the process repeated.

Note that after simulation is adjusted (step 152), an optional step 154can include inquiring with the patient as to how the adjustment feels,such as whether the adjustment seems to have reduced side effects suchas paresthesia. If so, the ECAP algorithm 124 could be stopped at thispoint (step 156), with the adjustment set as the new stimulation programfor the patient. Or, the ECAP algorithm 124 could be allowed to continueto see if even better therapeutic results can be achieved.

While the ECAP algorithm 124 can simply always be operable in the IPG100 or an ETS, it may be more sensible to enable its use only at varioustimes to improve an original stimulation program otherwise selected fora given patient. Occasional use of the ECAP algorithm 124 can beachieved using any external system that can communicate with the IPG 100or ETS, such as the clinician programmer system of FIG. 3 , or thepatient external controller 50 of FIG. 2 . Although not shown, such anexternal system can be programmed with a user interface programexecutable on an external device configured to communicate with themedical device, which when executed is configured to present an optionto allow a user of the external system (e.g., on its screen or display)to command the medical device to implement the ECAP algorithm 124, andperhaps also to disable use of the algorithm.

Further, at least some portions of the ECAP algorithm 124, or all of it,may operate on the external system. For example, the external system'scommunication circuitry may receive the detected neural response (ECAP);determine the shape parameters and assess them for relativesynchronicity; determine how to adjust the original stimulation programto promote desynchronicity; and transmit one or more controlinstructions to cause the medical device to adjust the stimulationprogram accordingly. Use of the ECAP algorithm 124 in conjunction withthe clinician programming system as the external system can occur duringan ETS phase, or even afterwards when an IPG has been fully implanted,such as when a patient meets with a clinician for a check-up.

One skilled in the art will understand that the ECAP algorithm 124and/or any supporting user interface program will comprise instructionsthat can be stored on non-transitory machine-readable media, such asmagnetic, optical, or solid-state memories. Such memories may be withinthe IPG or ETS itself (i.e., stored in association with controlcircuitry 102), within the external system, or readable by the externalsystem (e.g., memory sticks or disks). Such memories may also includethose within Internet or other network servers, such as an implantablemedical device manufacturer's server or an app store server, which maybe downloaded to the external system.

As noted, adjustment of the original stimulation program by the ECAPalgorithm 124 to promote desynchronicity (step 152, FIG. 9 ) can occurin several different manners, some of which are illustrated in FIGS. 10Athrough 15B. While these manners are described individually forsimplicity, it should be noted that any of the manners can be used incombination.

A first manner in which the ECAP algorithm 124 can adjust a patient'soriginal stimulation program to achieve improved desynchronicity isshown in FIGS. 10A and 10B. In this example, the ECAP algorithm 124 hasadded an additional active electrode to the stimulation program.Specifically, an electrode (E3) has been added to the originalstimulation program (which again comprises E4 as an anode and E5 as acathode in a simple example) as an additional anode. This additionalanode (E3) is preferably proximate to the other active electrodes (E4,E5) to be generally consistent with the location of needed therapy, butneed not be so. In the example shown, the amplitude of additional anodeE3 equals an amount (X) by which the amplitude of anode E4 is decreased.Thus, the ECAP algorithm 124's adjustment to the stimulation program inthis example does not vary the energy used to provide stimulationpulses, although this isn't strictly necessary. Anode E4 can retain itsoriginal amplitude, with the amplitude of E3 set in other manners.Regardless, note that the cathodic current at cathode electrode E5 mayor may not need adjustment to recover the sum of the anodic current atE4 and E3. Notice in this example that additional anode E3 otherwise hasthe same timing (pulse width, and frequency) as original activeelectrodes E4 and E5.

As shown in FIG. 10A, and when compared to FIGS. 8A, it is seen thatadding anode electrode E3 varies the size and shape of the electricfield 95 that forms in the patient's tissue. As a result, differentneurons will be recruited, and at different lengths along the lead,which should generally increase desynchronicity of the resulting ECAP.Although not shown, whether this adjustment has in fact increaseddesynchronicity can be verified by the ECAP algorithm 124 by detectingat the designated sense electrode(s) (e.g., E9; FIG. 8B) the shape ofthe resulting ECAP, as explained earlier. (The resulting ECAP at thesense electrode S is not shown in FIG. 10B for simplicity). If increaseddesynchronization is sensed, hopefully with the patient reporting goodtherapeutic results and less paresthesia, the ECAP algorithm 124 caneither keep running and making future adjustments as necessary, or theECAP algorithm 124 may stop running and set the adjustment as the newstimulation program for the patient. If increased desynchronization isnot sensed, the ECAP algorithm 124 can continuing running to make otheradjustments, such as by picking other additional anodes or cathodes, byvarying their amplitudes, or by other means discussed subsequently.

Although not shown in FIGS. 10A and 10B, realize that still anotheranode could be added by the ECAP algorithm 124 to try and increasedesynchronicity, or one or more additional cathodes could be added aswell. For example, E3 and/or E6 could be added as an additional cathode.

In the example of FIGS. 10A and 10B, additional anode or cathodeelectrodes issue pulses having the same timing as those specified by theoriginal stimulation program. However, such additional electrodes mayalso issue with different timings as well, as shown in FIGS. 11A and11B. In this example, ECAP algorithm 124 has again added an additionalanode electrode E3 to try and increase desynchronicity, but the pulse atE3 issues after the pulses otherwise provided by the originalstimulation program at electrodes E4 and E5 such that they arenon-overlapping. Notice that cathode electrode E5 is concurrentlymodified by the ECAP algorithm 124 to provide a return path for theadded anodic current issued by the additional anode E3. Although notillustrated, a different cathode electrode could be chosen to complimentadditional anode electrode E3. In fact, because the additional anodepulse at E3 is non-overlapping, a complementary cathodic pulse couldcomprise any electrode, including E4, even though E4 otherwise operatesas an anode in the original stimulation program. Further, although theadditional anode electrode is seen to issue a pulse with a pulse widthequal to those used in the original stimulation program, the additionalanode pulse width (PWa) could be different.

As shown in FIG. 11A, this example produces two electric fields at twodifferent times: a first field 95 a formed during the original pulses(E4 and E5), and a second field 95 b formed by the pulses involving theadditional anode (E3 and E5). As such, different neurons will berecruited by the different electric fields, and will fire at differentpoints in time. This will increase desynchronicity, as verifiable viathe ECAP algorithm 124, hopefully with good therapeutic results andreduced side effects. Again, although not illustrated, one or moreadditional anodes, or one or more additional cathodes, could be chosenby ECAP algorithm 124 to try and increase desynchronicity. Additionalfurther pulses could also issue that are non-overlapping with the pulsesat E3, E4, or E5, although this isn't shown.

FIGS. 12A and 12B illustrate another manner in which ECAP algorithm 124can attempt to increase desynchronicity, by choice of an additionalanode or cathode electrode that issue a pulse that unlike FIGS. 11A and11B is at least partially overlapping with the pulses of the originalstimulation program. Specifically and as shown, the first phase of thepulse at additional anode E3 overlaps with the second phase of theoriginal stimulation pulses. This is not strictly necessary; the firstphase of the additional pulse may overlap with the first phase of theoriginal pulses as well. Further, the pulse width (PWa) of theadditional pulse may again be different from the pulse width of theoriginal pulses, as occurred in FIGS. 11A and 11B. Once again, thisstrategy produces different electric fields between fields 95 a and 95 bat different points in time, thus recruiting different neurons atdifferent points in time and promoting desynchronicity. Still otheroverlapping pulses could be added as well.

FIGS. 13A and 13B illustrate an example in which an additional anodeissues pulses with a different frequency (f2) than the originalstimulation pulses (f1). Again, this will recruit neurons at differenttimes, thus promoting desynchronicity. Again, modifications discussed inconjunction with earlier examples (use of further additional anodes oradditional cathode(s), different pulse widths, overlapping ornon-overlapping pulses, etc.) could be used here as well.

Promoting desynchronicity via ECAP algorithm 124 may not involveadjustments to an original stimulation program that involve the use ofadditional anodes or cathodes, as illustrated to this point. Instead,adjustment may involve adjustments using the original active electrodes(e.g., E4 and E5), and a first example is shown in FIGS. 14A and 14B. Asshown in FIG. 14B, the ECAP algorithm 124 has adjusted the amplitude (A)of the original pulses to make them different at different points intime. Specifically, the pulses have been adjusted to have a plurality ofdifferent amplitudes, and in this example have been split into portionshaving amplitudes A1 and A2. As shown, A1 and A2 are respectively lowerand higher than the original amplitude A by the same amount, and thusrequire the same energy as the original pulses, but again this is notstrictly necessary. The pulse portion of amplitude A1 produces anelectric field 95 a of a first volume (or strength), while amplitude A2produces a larger volume (or larger strength) field 95 b that wouldrecruit additional neurons, thus promoting desynchronicity in neuronalfiring.

In the example of FIGS. 15A and 15B, the adjustment provided by the ECAPalgorithm 124 again involves only the original active electrodes E4 andE5, but in which the pulse width of the original stimulation pulses isadjusted from PW to PW1. In this example, the pulse width PW1 isapproximately half of the original pulse width PW, and so two biphasicpulses can be formed over the same time duration. This is merely anexample though, more than two pulses could be formed, and the pulsesformed by adjustment need not occupy the same time duration as theoriginal pulses. Notice in effect that the original pulses in thisexample have been adjusted into groups (G) of pulses with frequencies(f2) that are higher than the frequency of the original stimulationpulses (f1) in an attempt to increase desynchronicity.

Although particular embodiments have been shown and described, the abovediscussion should not limit the present invention to these embodiments.Various changes and modifications may be made without departing from thespirit and scope of the present invention. Thus, the present inventionis intended to cover equivalent embodiments that may fall within thescope of the present invention as defined by the claims.

What is claimed is:
 1. A method for controlling stimulation in a medicaldevice comprising a plurality of electrodes configured to providestimulation for a patient's tissue, the method comprising: (a) issuingstimulation pulses pursuant to a stimulation program at at least twoelectrodes of the plurality of electrodes, and detecting a first neuralresponse to the stimulation pulses at at least one electrode of theplurality of electrodes different from the at least two electrodes thatissue the stimulation pulses; (b) determining a height and/or width thefirst neural response; (c) if the height of the first neural response isabove a first threshold and/or if the width of the first neural responseis below a second threshold, adjusting the stimulation program to issueadjusted pulses at the at least two electrodes of the plurality ofelectrodes, and detecting a second neural response to the adjustedpulses at the at least one electrode; (d) determining a height and/orwidth of the second neural response; and (e) verifying that the heightof the second neural response is below the first threshold and/or thatthe width of the second neural response is above the second threshold.2. The method of claim 1, further comprising: (f) verifying that theadjusted pulses produce less paresthesia in the patient than thestimulation pulses.
 3. The method of claim 1, wherein the first andsecond neural responses comprise Evoked Compound Action Potentials(ECAPs).
 4. The method of claim 1, further comprising prior to step (a)selecting the at least one electrode relative to the at least two activeelectrodes.
 5. The method of claim 1, wherein the adjusted pulses have adifferent amplitude than the stimulation pulses, or wherein the adjustedpulses have a different pulse width than the stimulation pulses, orwherein the adjusted pulses have a different frequency than thestimulation pulses.
 6. The method of claim 1, wherein adjusting thestimulation program comprises adding to the at least two activeelectrodes an additional electrode that issues the adjusted pulses. 7.The method of claim 6, wherein the adjusted pulses at the additionalelectrode do not overlap with the adjusted pulses at the at least twoelectrodes.
 8. The method of claim 6, wherein the adjusted pulses at theadditional electrode overlaps with the adjusted pulses at the at leasttwo electrodes.
 9. The method of claim 6, wherein the adjusted pulses atthe additional electrode only partially overlap with the adjusted pulsesat the at least two electrodes.
 10. The method of claim 1, wherein thestimulation pulses have a first frequency, and wherein adjusting thestimulation program comprises issuing the adjusted pulses as groups,wherein each group of the adjusted pulses has a second frequency higherthan the first frequency.
 11. A system, comprising: a medical devicecomprising a plurality of electrodes configured to provide stimulationfor a patient's tissue; and a machine-implementable algorithm, whereinthe algorithm when executed is configured to (a) issue stimulationpulses pursuant to a stimulation program at at least two electrodes ofthe plurality of electrodes, and detect a first neural response to thestimulation pulses at at least one electrode of the plurality ofelectrodes different from the at least two electrodes that issue thestimulation pulses; (b) determine a height and/or width of the firstneural response; (c) adjust the stimulation program to issue adjustedpulses at the at least two electrodes of the plurality of electrodes,and detect a second neural response to the adjusted pulses at the atleast one electrode; (d) determine a height and/or width of the secondneural response; and (e) verify that the height of the second neuralresponse is below the first threshold and/or that the width of thesecond neural response is above the second threshold.
 12. The system ofclaim 11, wherein the algorithm when executed is further configured to(f) receive an indication that the adjusted pulses produce lessparesthesia in the patient than the stimulation pulses.
 13. The systemof claim 11, wherein the algorithm is stored on a non-transitorymachine-readable medium within the medical device, and wherein thealgorithm is configured to be executed within the medical device. 14.The system of claim 11, further comprising an external system configuredto communicate with the medical device.
 15. The system of claim 14,further comprising a user interface program executable on the externalsystem, wherein the user interface program is configured to present anoption to allow a user of the external system to command the medicaldevice to implement the algorithm in the medical device.
 16. The systemof claim 15, wherein the user interface program is further configured toallow the user to disable use of the algorithm in the medical device.17. The system of claim 14, wherein the algorithm is stored on anon-transitory machine-readable medium within the external system, andwherein the algorithm is configured to be executed within the externalsystem.
 18. The system of claim 17, wherein the external system furthercomprises communication circuitry configured to: receive the first andsecond neural responses from the medical device, and transmit one ormore control instructions to control stimulation circuitry in themedical device to issue the adjusted pulses.
 19. The system of claim 18,wherein the external system comprises a clinician programmer system or ahand-held external controller for the medical device.
 20. The system ofclaim 11, wherein the medical device comprises an implantable pulsegenerator or an external stimulator.